Methods and Systems for Mapping Local Conduction Velocity

ABSTRACT

The local conduction velocity of a cardiac activation wavefront can be computed by collecting a plurality of electrophysiology (“EP”) data points using a multi-electrode catheter, with each EP data point including both position data and local activation time (“LAT”) data. For any EP data point, a neighborhood of EP data points, including the selected EP data point and at least two additional EP data points, can be defined. Planes of position and LATs can then be defined using the positions and LATs, respectively, of the EP data points within the neighborhood. A conduction velocity can be computed from an intersection of the planes of positions and LATs. The resultant plurality of conduction velocities can be output as a graphical representation (e.g., an electrophysiology map), for example by displaying vector icons arranged in a uniform grid over a three-dimensional cardiac model.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No.15/278,092, filed 28 Sep. 2016 (the '092 application), now pending,which is a continuation of U.S. application Ser. No. 14/884,534, filed15 Oct. 2015 (the '534 application), now U.S. Pat. No. 9,474,491, whichin turn claims the benefit of and priority to U.S. application No.62/063,987, filed 15 Oct. 2014 (the '987 application). The '092application, '534 application, and '987 application are each herebyincorporated by reference as though fully set forth herein.

BACKGROUND

The instant disclosure relates to electrophysiological mapping, such asmay be performed in cardiac diagnostic and therapeutic procedures. Inparticular, the instant disclosure relates to systems, apparatuses, andmethods for computing local conduction velocities from data collected byan electrophysiology probe (e.g., a contact or non-contact mappingcatheter).

Two mainstay hypotheses of arrhythmia maintenance mechanisms are singlesource focus and circus movement reentry. To study both mechanisms andidentify the conduction circuits that sustain the arrhythmia, it isdesirable to map both activation direction and activation speed duringthe arrhythmia.

It is known to use an isochrone map based on local activation time(“LAT”) to map the propagation of a cardiac activation wavefront. Toproduce such a map, however, there must be a common activation timereference, which is normally a stable cardiac detection. Thus,isochronal maps of LATs are typically limited to cardiac-triggered maps.

BRIEF SUMMARY

Disclosed herein is a method of computing local conduction velocity of acardiac activation wavefront, including: collecting a plurality ofelectrophysiology (“EP”) data points using a multi-electrode catheter,each EP data point of the plurality of EP data points including positiondata and local activation time (“LAT”) data; selecting an EP data pointfrom the plurality of EP data points; defining a neighborhood of EP datapoints including the selected EP data point and at least two additionalEP data points from the plurality of EP data points; defining a plane ofpositions using the positions of the EP data points within theneighborhood of EP data points; defining a plane of LATs using the LATsof the EP data points within the neighborhood of EP data points; andcomputing a conduction velocity for the selected EP data point from anintersection of the plane of positions and the plane of LATs if theplane of positions and the plane of LATs intersect. These steps can berepeated for a plurality of EP data points, thereby computing aplurality of conduction velocities. These plurality of conductionvelocities can then be output as a three-dimensional graphicalrepresentation, such as by using a plurality of conduction velocityvector icons arranged in a uniform grid over a three-dimensional modelof at least a portion of a heart.

In certain aspects, the LATs for the plurality of EP data points arecomputed relative to activation at a stable reference electrode. Inother aspects, they are computed relative to activation at an electrodecarried by the multi-electrode catheter.

The step of computing a conduction velocity for the selected EP datapoint from an intersection of the plane of positions and the plane ofLATs can include: computing a plurality of conduction velocityconstituents for the selected EP data point, each of the plurality ofconduction velocity constituents corresponding to a conduction velocityduring one of a plurality of activation windows of a time segment; andcomputing a composite conduction velocity over the time segment for theselected EP data point from the plurality of conduction velocityconstituents. Computing a plurality of conduction velocity constituentsfor the selected EP data point can, in turn, include: selecting anelectrode carried by the multi-electrode catheter as a referenceelectrode, the reference electrode having an associated referenceelectrophysiological signal; detecting a plurality of activations withinthe reference electrophysiological signal; defining a plurality ofactivation windows, wherein each of the plurality of activation windowscontains one of the detected plurality of activations; and, for each ofthe plurality of activation windows: defining the plane of positions andthe plane of LATs for the selected EP data point; and computing theconduction velocity constituent for the selected EP data point from theintersection of the plane of positions and the plane of LATs for theselected EP data point, thereby computing the plurality of conductionvelocity constituents for the selected EP data point.

According to embodiments disclosed herein, the electrode carried by themulti-electrode catheter that is selected as a reference electrode canbe the electrode having a greatest number of activations within the timesegment as the reference electrode.

It is contemplated that the composite conduction velocity over the timesegment can be computed as the mean of the plurality of conductionvelocity constituents. Alternatively, the composite conduction velocityover the time segment can be a dominant conduction velocity selected orcomputed from the plurality of conduction velocity constituents.

In other embodiments, a conduction velocity consistency index indicatinga degree of consistency in a direction of the conduction velocityconstituents for a selected EP data point can be computed. Theconduction velocity consistency index can include a ratio of an absolutemagnitude of the composite conduction velocity and an average absolutemagnitude of the conduction velocity constituents, a ratio of anabsolute magnitude of the composite conduction velocity and an absolutemagnitude of an average of the conduction velocity constituents, anaverage normalized dot product of the conduction velocity constituentsand the composite conduction velocity, and/or a weighting factor. Theweighting factor can account for the number of activation windows forwhich a valid conduction velocity constituent was computed (e.g., thoseactivation windows where the plane of positions and the plane of LATsintersected).

The plane of positions can be defined from a least squares fit of thepositions of the EP data points in the neighborhood of EP data points.Similarly, the plane of LATs can be defined from a least squares fit ofthe positions of pseudo-EP data points, the coordinates of which can bedefined by a position of the corresponding EP data point within theplane of positions and the LAT for the corresponding data point.

Also disclosed herein is a system for computing local conductionvelocity of a cardiac activation wavefront, including: a conductionvelocity processor configured to receive as input a plurality ofelectrophysiology (“EP”) data points collected using a multi-electrodecatheter, each EP data point of the plurality of EP data points having aposition and a local activation time (“LAT”), and, for a selected EPdata point of the plurality of EP data points: define a neighborhood ofEP data points including the selected EP data point and at least twoadditional EP data points from the plurality of EP data points; define aplane of positions using the positions of the EP data points within theneighborhood of EP data points; define a plane of LATs using the LATs ofthe EP data points within the neighborhood of EP data points; andcompute a conduction velocity from an intersection of the plane ofpositions and the plane of LATs, if the plane of positions and the planeof LATs intersect; and a mapping processor configured to generate athree-dimensional graphical representation of a plurality of conductionvelocities computed by the conduction velocity processor.

In yet another aspect, a method of computing local conduction velocityof a cardiac activation wavefront from a plurality of electrophysiology(“EP”) data points includes: selecting an EP data point from theplurality of EP data points; defining a neighborhood of EP data pointsincluding the selected EP data point and at least two additional EP datapoints from the plurality of EP data points; defining a plane ofpositions using the positions of the EP data points within theneighborhood of EP data points; defining a plane of LATs using the LATsof the EP data points within the neighborhood of EP data points; andcomputing a conduction velocity for the selected EP data point from anintersection of the plane of positions and the plane of LATs if theplane of positions and the plane of LATs intersect.

The foregoing and other aspects, features, details, utilities, andadvantages of the present invention will be apparent from reading thefollowing description and claims, and from reviewing the accompanyingdrawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic of an electrophysiology system, such as may beused in an electrophysiology study.

FIG. 2 depicts an exemplary multi-electrode catheter used in anelectrophysiology study.

FIG. 3 is a flowchart of representative steps that can be followed tocreate a conduction velocity map.

FIG. 4 is an exemplary conduction velocity map according to anembodiment disclosed herein.

FIG. 5 is a flowchart of representative steps that can be followed tocreate a conduction velocity map in the case of irregular cardiacactivations.

DETAILED DESCRIPTION

The present disclosure provides methods, apparatuses, and systems forthe creation of electrophysiology maps (e.g., electrocardiographic maps)that provide information regarding the local conduction velocity of acardiac activation wavefront. Advantageously, because local conductionvelocity is reference-independent, the teachings herein can be appliedto compute local conduction velocity for both regular activations(including both sinus rhythm and regular cardiac arrhythmias) andirregular activations (such as irregular arrhythmias, including atrialfibrillation), where a stable reference may not be available.

FIG. 1 shows a schematic diagram of an electrophysiology system 8 forconducting cardiac electrophysiology studies by navigating a cardiaccatheter and measuring electrical activity occurring in a heart 10 of apatient 11 and three-dimensionally mapping the electrical activityand/or information related to or representative of the electricalactivity so measured. System 8 can be used, for example, to create ananatomical model of the patient's heart 10 using one or more electrodes.System 8 can also be used to measure electrophysiology data, including,but not limited to, local activation time (“LAT”), at a plurality ofpoints along a cardiac surface and store the measured data inassociation with location information for each measurement point atwhich the electrophysiology data was measured, for example to create adiagnostic data map of the patient's heart 10.

As one of ordinary skill in the art will recognize, and as will befurther described below, system 8 can determine the location, and insome aspects the orientation, of objects, typically within athree-dimensional space, and express those locations as positioninformation determined relative to at least one reference.

For simplicity of illustration, the patient 11 is depicted schematicallyas an oval. In the embodiment shown in FIG. 1, three sets of surfaceelectrodes (e.g., patch electrodes) are shown applied to a surface ofthe patient 11, defining three generally orthogonal axes, referred toherein as an x-axis, a y-axis, and a z-axis. In other embodiments theelectrodes could be positioned in other arrangements, for examplemultiple electrodes on a particular body surface. As a furtheralternative, the electrodes do not need to be on the body surface, butcould be positioned internally to the body or on an external frame.

In FIG. 1, the x-axis surface electrodes 12, 14 are applied to thepatient along a first axis, such as on the lateral sides of the thoraxregion of the patient (e.g., applied to the patient's skin underneatheach arm) and may be referred to as the Left and Right electrodes. They-axis electrodes 18, 19 are applied to the patient along a second axisgenerally orthogonal to the x-axis, such as along the inner thigh andneck regions of the patient, and may be referred to as the Left Leg andNeck electrodes. The z-axis electrodes 16, 22 are applied along a thirdaxis generally orthogonal to both the x-axis and the y-axis, such asalong the sternum and spine of the patient in the thorax region, and maybe referred to as the Chest and Back electrodes. The heart 10 liesbetween these pairs of surface electrodes 12/14, 18/19, and 16/22.

An additional surface reference electrode (e.g., a “belly patch”) 21provides a reference and/or ground electrode for the system 8. The bellypatch electrode 21 may be an alternative to a fixed intra-cardiacelectrode 31, described in further detail below. It should also beappreciated that, in addition, the patient 11 may have most or all ofthe conventional electrocardiogram (“ECG” or “EKG”) system leads inplace. In certain embodiments, for example, a standard set of 12 ECGleads may be utilized for sensing electrocardiograms on the patient'sheart 10. This ECG information is available to the system 8 (e.g., itcan be provided as input to computer system 20). Insofar as ECG leadsare well understood, and for the sake of clarity in the figures, onlyone lead 6 and its connection to computer system 20 is illustrated inFIG. 1.

A representative catheter 13 having at least one electrode 17 (e.g., adistal electrode) is also depicted in schematic fashion in FIG. 1. Thisrepresentative catheter electrode 17 can be referred to as a“measurement electrode” or a “roving electrode.” Typically, multipleelectrodes on catheter 13, or on multiple such catheters, will be used.In one embodiment, for example, system 8 may utilize sixty-fourelectrodes on twelve catheters disposed within the heart and/orvasculature of the patient.

In other embodiments, system 8 may utilize a single catheter thatincludes multiple (e.g., eight) splines, each of which in turn includesmultiple (e.g., eight) electrodes. Of course, these embodiments aremerely exemplary, and any number of electrodes and catheters may beused. Indeed, in some embodiments, a high density mapping catheter, suchas the EnSite™ Array™ non-contact mapping catheter of St. Jude Medical,Inc., can be utilized.

Likewise, it should be understood that catheter 13 (or multiple suchcatheters) are typically introduced into the heart and/or vasculature ofthe patient via one or more introducers and using familiar procedures.For purposes of this disclosure, a segment of an exemplarymulti-electrode catheter 13 is shown in FIG. 2. In FIG. 2, catheter 13extends into the left ventricle 50 of the patient's heart 10 through atransseptal sheath 35. The use of a transseptal approach to the leftventricle is well known and will be familiar to those of ordinary skillin the art, and need not be further described herein. Of course,catheter 13 can also be introduced into the heart 10 in any othersuitable manner.

Catheter 13 includes electrode 17 on its distal tip, as well as aplurality of additional measurement electrodes 52, 54, 56 spaced alongits length in the illustrated embodiment. Typically, the spacing betweenadjacent electrodes will be known, though it should be understood thatthe electrodes may not be evenly spaced along catheter 13 or of equalsize to each other. Since each of these electrodes 17, 52, 54, 56 lieswithin the patient, location data may be collected simultaneously foreach of the electrodes by system 8.

Similarly, each of electrodes 17, 52, 54, and 56 can be used to gatherelectrophysiological data from the cardiac surface. The ordinarilyskilled artisan will be familiar with various modalities for theacquisition and processing of electrophysiology data points (including,for example, both contact and non-contact electrophysiological mapping),such that further discussion thereof is not necessary to theunderstanding of the conduction velocity mapping techniques disclosedherein. Likewise, various techniques familiar in the art can be used togenerate a graphical representation from the plurality ofelectrophysiology data points. Insofar as the ordinarily skilled artisanwill appreciate how to create electrophysiology maps fromelectrophysiology data points, the aspects thereof will only bedescribed herein to the extent necessary to understand the mapsdisclosed herein.

Returning now to FIG. 1, in some embodiments, a fixed referenceelectrode 31 (e.g., attached to a wall of the heart 10) is shown on asecond catheter 29. For calibration purposes, this electrode 31 may bestationary (e.g., attached to or near the wall of the heart) or disposedin a fixed spatial relationship with the roving electrodes (e.g.,electrodes 17, 52, 54, 56), and thus may be referred to as a“navigational reference” or “local reference.” The fixed referenceelectrode 31 may be used in addition or alternatively to the surfacereference electrode 21 described above. In many instances, a coronarysinus electrode or other fixed electrode in the heart 10 can be used asa reference for measuring voltages and displacements; that is, asdescribed below, fixed reference electrode 31 may define the origin of acoordinate system.

Each surface electrode is coupled to a multiplex switch 24, and thepairs of surface electrodes are selected by software running on acomputer 20, which couples the surface electrodes to a signal generator25. Alternately, switch 24 may be eliminated and multiple (e.g., three)instances of signal generator 25 may be provided, one for eachmeasurement axis (that is, each surface electrode pairing).

The computer 20, for example, may comprise a conventionalgeneral-purpose computer, a special-purpose computer, a distributedcomputer, or any other type of computer. The computer 20 may compriseone or more processors 28, such as a single central processing unit(CPU), or a plurality of processing units, commonly referred to as aparallel processing environment, which may execute instructions topractice the various aspects disclosed herein.

Generally, three nominally orthogonal electric fields are generated by aseries of driven and sensed electric dipoles (e.g., surface electrodepairs 12/14, 18/19, and 16/22) in order to realize catheter navigationin a biological conductor. Alternatively, these orthogonal fields can bedecomposed and any pairs of surface electrodes can be driven as dipolesto provide effective electrode triangulation. Likewise, the electrodes12, 14, 18, 19, 16, and 22 (or any other number of electrodes) could bepositioned in any other effective arrangement for driving a current toor sensing a current from an electrode in the heart. For example,multiple electrodes could be placed on the back, sides, and/or belly ofpatient 11. For any desired axis, the potentials measured across theroving electrodes resulting from a predetermined set of drive(source-sink) configurations may be combined algebraically to yield thesame effective potential as would be obtained by simply driving auniform current along the orthogonal axes.

Thus, any two of the surface electrodes 12, 14, 16, 18, 19, 22 may beselected as a dipole source and drain with respect to a groundreference, such as belly patch 21, while the unexcited electrodesmeasure voltage with respect to the ground reference. The rovingelectrodes 17, 52, 54, 56 placed in the heart 10 are exposed to thefield from a current pulse and are measured with respect to ground, suchas belly patch 21. In practice the catheters within the heart 10 maycontain more or fewer electrodes than the four shown, and each electrodepotential may be measured. As previously noted, at least one electrodemay be fixed to the interior surface of the heart to form a fixedreference electrode 31, which is also measured with respect to ground,such as belly patch 21, and which may be defined as the origin of thecoordinate system relative to which localization system 8 measurespositions. Data sets from each of the surface electrodes, the internalelectrodes, and the virtual electrodes may all be used to determine thelocation of the roving electrodes 17, 52, 54, 56 within heart 10.

The measured voltages may be used by system 8 to determine the locationin three-dimensional space of the electrodes inside the heart, such asroving electrodes 17, 52, 54, 56, relative to a reference location, suchas reference electrode 31. That is, the voltages measured at referenceelectrode 31 may be used to define the origin of a coordinate system,while the voltages measured at roving electrodes 17, 52, 54, 56 may beused to express the location of roving electrodes 17, 52, 54, 56relative to the origin. In some embodiments, the coordinate system is athree-dimensional (x, y, z) Cartesian coordinate system, although othercoordinate systems, such as polar, spherical, and cylindrical coordinatesystems, are contemplated.

As should be clear from the foregoing discussion, the data used todetermine the location of the electrode(s) within the heart is measuredwhile the surface electrode pairs impress an electric field on theheart. The electrode data may also be used to create a respirationcompensation value used to improve the raw location data for theelectrode locations as described in U.S. Pat. No. 7,263,397, which ishereby incorporated herein by reference in its entirety. The electrodedata may also be used to compensate for changes in the impedance of thebody of the patient as described, for example, in U.S. Pat. No.7,885,707, which is also incorporated herein by reference in itsentirety.

In one representative embodiment, the system 8 first selects a set ofsurface electrodes and then drives them with current pulses. While thecurrent pulses are being delivered, electrical activity, such as thevoltages measured with at least one of the remaining surface electrodesand in vivo electrodes, is measured and stored. Compensation forartifacts, such as respiration and/or impedance shifting, may beperformed as indicated above.

In some embodiments, system 8 is the EnSite™ Velocity™ cardiac mappingand visualization system of St. Jude Medical, Inc., which generateselectrical fields as described above, or another such system that reliesupon electrical fields. Other systems, however, may be used inconnection with the present teachings, including for example, the CARTOnavigation and location system of Biosense Webster, Inc., the AURORA®system of Northern Digital Inc., or Sterotaxis' NIOBE® MagneticNavigation System, all of which utilize magnetic fields rather thanelectrical fields. The localization and mapping systems described in thefollowing patents (all of which are hereby incorporated by reference intheir entireties) can also be used with the present invention: U.S. Pat.Nos. 6,990,370; 6,978,168; 6,947,785; 6,939,309; 6,728,562; 6,640,119;5,983,126; and 5,697,377.

One basic methodology of computing local conduction velocity will beexplained with reference to the flowchart of representative stepspresented as FIG. 3. In some embodiments, for example, the flowchart mayrepresent several exemplary steps that can be carried out by thecomputer 20 of FIG. 1 (e.g., by one or more processors 28) to generate aconduction map such as described herein. It should be understood thatthe representative steps described below can be either hardware- orsoftware-implemented. For the sake of explanation, the term “signalprocessor” is used herein to describe both hardware- and software-basedimplementations of the teachings herein.

In step 302, a plurality of electrophysiology (“EP”) data points arecollected, for example using a multi-electrode catheter 13 as describedabove. As will be familiar to the person of ordinary skill in the art,and as described above, each EP data point will include locationinformation and EP information, including, without limitation, LATinformation.

In block 304, one of the EP data points is selected for computation oflocal conduction velocity. Then, in block 306, a neighborhood of EP datapoints, including the EP data point selected in block 304 and at leasttwo additional data points, is defined. The size of the neighborhood ofEP data points can be user selected based, for example, upon the spatialdensity of the electrodes carried by multi-electrode catheter 13. Thatis, as electrode density increases, the user can decrease the size ofthe neighborhood of EP data points. Alternatively, and in otherembodiments, the neighborhood of EP data points can be selectedautomatically via criteria pre-programmed within the computer system 20and/or provided by another component.

In blocks 308 and 310, two different planes are computed from theneighborhood of EP data points. In block 308, a plane of positions iscomputed using the positions of the EP data points within theneighborhood. For example, the plane of positions can be computed from aleast squares fit of the positions of the EP data points within theneighborhood of EP data points.

Similarly, in block 310, a plane of LATs is computed using the positionsof the EP data points within the neighborhood. For example, in oneaspect, a new pseudo-EP data point is defined for each of the EP datapoints within the neighborhood. For each pseudo-EP data point, two ofthe coordinates are determined by the in-plane position of the EP datapoint, such as computed when computing the plane of positions. The thirdcoordinate, which can be normal to the plane of positions, can be thevalue of the LAT for the EP data point. The plane of LATs can becomputed from a least squares fit of the positions of the pseudo-EP datapoints.

Block 312 checks whether the plane of positions and the plane of LATsintersect. If they do not intersect, then in block 314, the localconduction velocity for the selected EP data point is set to“undefined.” If, however, the two planes do intersect, then theintersection of planes is used to compute the local conduction velocity(i.e., magnitude and direction) at the selected EP data point in block316. In some embodiments, the direction of the local conduction velocityis normal to the line of intersection between the plane of positions andthe plane of LATs, while the magnitude of the local conduction velocitycan be computed as the cotangent of the angle between the plane ofpositions and the plane of LATs.

The process can then repeat from the selection of an EP data point inblock 304 to compute a plurality of local conduction velocities for asmany as all of the EP data points collected in block 302.

Once a plurality of local conduction velocities have been computed, theycan be output as a three-dimensional conduction velocity map in block318. An exemplary conduction velocity map 400 is shown in FIG. 4, whichincludes a plurality of velocity vector icons 402. The arrowheads onvector icons 402 show the direction of the activation wavefront, whilethe size of vector icons 402 reflect the magnitude of the conductionvelocity.

FIG. 4 further illustrates that the vector icons 402 can be arranged ina uniform grid so that adjacent icons 402 do not obscure each other.That is, rather than showing a vector icon 402 at each EP data point,which construct might lead to overlapping icons 402 and an illegiblepresentation, the surface of cardiac model 404 can be divided into auniform grid having a user-determined grid size. A single vector icon402 can be displayed in each grid square, with the magnitude anddirection determined, for example, by interpolation from the conductionvelocities computed at nearby EP data points. Of course, it is withinthe spirit and scope of the instant disclosure to display vector icons402 at each EP data point for which a valid conduction velocity wascomputed.

For regular activations, such as during sinus rhythm or for regularcardiac arrhythmias, LATs can be computed relative to activation at astable reference electrode, such as fixed reference electrode 31.Alternatively, one of the electrodes on multi-electrode catheter 13 canbe selected as a reference for the computation of LATs (the selectedreference electrode should itself have a validly computed LAT).

In the case of an irregular arrhythmia, however, there is often nostable activation detection that can be used as a reference for LATs.Advantageously, however, the method of computing local conductionvelocities described above can be adapted to compute local conductionvelocities even in the case of irregular arrhythmias. An exemplaryadaptation will be described with reference to FIG. 5.

The initial steps shown in FIG. 5 are common with the initial stepsshown in FIG. 3. That is, EP data points are collected in block 302, oneEP data point is selected in block 304 for the computation of a localconduction velocity, and a neighborhood of EP data points is defined inblock 306. The local conduction velocity at the selected EP data point,however, is computed as a composite from a plurality of conductionvelocity constituents as described below.

In block 502, a time segment within which the composite conductionvelocity will be computed is defined. For example, in certain aspects,the time segment is 8 seconds long, though this duration is merelyexemplary and not limiting.

In block 504, one of the electrodes on multi-electrode catheter 13 isselected as an time reference for the time segment. In one embodiment,an activation detection algorithm is applied to the EP signal detectedby each electrode on multi-electrode catheter 13 (that is, eachintra-cardiac electrogram (“EGM”) is signal processed), and theelectrode having the greatest number of activations (that is, theelectrode whose EGM has the smallest mean cycle length) over the timesegment is selected as the time reference. Other methods of selecting atime reference are, however, contemplated.

Once a time reference is selected, the EGM for the time reference isdivided into a plurality of activation windows over the time segment inblock 506. Each activation window contains one activation. Eachactivation window can be centered at the activation contained therein,with the width of the window being user-selected.

The several activation windows are then used to compute a correspondingnumber of conduction velocity constituents for the selected EP datapoint. The computation of a conduction velocity constituent generallyfollows the process described above with respect to FIG. 3 (e.g.,computing planes of position and LATs and then computing conductionvelocity from the intersection of these planes), with each computationrelative to a given activation window instead of the entire timesegment. Because the steps as shown in FIG. 5 are therefore analogous tothose shown in FIG. 3, the same reference numerals are used in FIG. 5 asin FIG. 3, with a “prime” designation (′) used to indicate applicabilityto an activation window instead of a full signal.

Once conduction velocity constituents for each activation window havebeen computed, a composite conduction velocity for the selected EP datapoint during the time segment is computed in block 508. In certainembodiments, the composite conduction velocity is computed as themathematical mean of the conduction velocity constituents

$\left( {{i.e.},{\frac{1}{N}{\sum_{i = 1}^{N}\overset{\rightarrow}{{CV}_{l}}}}} \right).$

where N is the number of activation windows for which a conductionvelocity was defined (i.e., where the plane of positions and the planeof LATs intersected), and {right arrow over (CV)}_(i) is the conductionvelocity constituent within the i^(th) activation window). In otherembodiments, the dominant conduction velocity constituent is selected asthe composite conduction velocity.

It is also contemplated that a conduction velocity consistency index canbe computed from the conduction velocity constituents. The conductionvelocity consistency index is a measure of the degree of consistency inthe direction of the conduction velocity constituents for a given EPdata point over the time segment. Thus, a high conduction velocityconsistency index can be associated with a high degree of directionalconsistency, while a lower conduction velocity consistency index can beassociated with a low degree of directional consistency (that is, a highdegree of randomness in the direction of the conduction velocityconstituents).

One way to compute a conduction velocity consistency index is as a ratioof the absolute magnitude of the composite conduction velocity (onesuitable formula for which is described above) and the average absolutemagnitude of the conduction velocity constituents (i.e., the averageconduction speed, or

$\left. {\frac{1}{N}{\sum_{i = 1}^{N}{\overset{\rightarrow}{{CV}_{l}}}}} \right).$

Another way to compute a conduction velocity consistency index is as aratio of the absolute magnitude of the composite conduction velocity(one suitable formula for which is described above) and the absolutemagnitude of the average of the conduction velocity constituents.

Still another way to compute a conduction velocity consistency index isas the average normalized dot product of the conduction velocityconstituents with the composite conduction velocity.

A weighting factor, which can be a further ratio of N to the totalnumber of activation windows, can also be included in the computation ofa conduction velocity consistency index.

The conduction velocity consistency index can also be graphicallydisplayed, such as on the exemplary conduction velocity map of FIG. 4.For example, the width of vector icon 402 can vary according to theconduction velocity consistency index.

Although several embodiments of this invention have been described abovewith a certain degree of particularity, those skilled in the art couldmake numerous alterations to the disclosed embodiments without departingfrom the spirit or scope of this invention.

For example, the plurality of computed local conduction velocities,and/or the resultant vector icons, can be used to determine the cardiacactivation wavefront propagation trajectory.

As another example, although the conduction velocity map is described asa static map, it is contemplated that, in some embodiments, the map canbe animated in order to show the propagation of the activationwavefront. Similarly, where the cardiac activation wavefront propagationtrajectory is determined from the conduction velocities, that trajectorycan also be displayed, highlighted, and/or animated on the map.

As yet another example, pattern recognition algorithms can be applied toidentify special cardiac activation wavefront propagation patterns, suchas linear, rotational, or focal patterns. Certain patterns, which may beuseful for diagnosis purposes, can then be highlighted on the map.

As a still further example, a spatial continuity index can be computedfrom the conduction velocities of adjacent EP data points (or, in thecase of a uniform grid display, adjacent grid squares). The spatialcontinuity index is reflective of the consistency of the direction inwhich the activation wavefront is propagating within a particular regionof the cardiac surface, with higher values of the index generallycorresponding to a higher degree of uniformity in propagation directionand lower values of the index generally corresponding to a higher degreeof wave front breakups in propagation direction.

All directional references (e.g., upper, lower, upward, downward, left,right, leftward, rightward, top, bottom, above, below, vertical,horizontal, clockwise, and counterclockwise) are only used foridentification purposes to aid the reader's understanding of the presentinvention, and do not create limitations, particularly as to theposition, orientation, or use of the invention. Joinder references(e.g., attached, coupled, connected, and the like) are to be construedbroadly and may include intermediate members between a connection ofelements and relative movement between elements. As such, joinderreferences do not necessarily infer that two elements are directlyconnected and in fixed relation to each other.

It is intended that all matter contained in the above description orshown in the accompanying drawings shall be interpreted as illustrativeonly and not limiting. Changes in detail or structure may be madewithout departing from the spirit of the invention as defined in theappended claims.

1-20. (canceled)
 21. A system for computing local conduction velocity ofa cardiac activation wavefront, comprising: a conduction velocityprocessor configured to receive as input a plurality ofelectrophysiology (“EP”) data points, each comprising position data andlocal activation time (“LAT”) data, collected using a multi-electrodecatheter, and, for a selected EP data point: define a neighborhood of EPdata points including the selected EP data point and at least twoadditional EP data points from the plurality of EP data points; andcompute a conduction velocity for the selected EP data point using theposition data of the neighborhood of EP data points and the LAT data ofthe neighborhood of EP data points.
 22. The system according to claim21, further comprising a mapping processor configured to generate athree-dimensional graphical representation of a plurality of conductionvelocities computed by the conduction velocity processor.
 23. The systemaccording to claim 22, wherein the three-dimensional graphicalrepresentation includes a plurality of conduction velocity vector iconsarranged in a uniform grid over a three-dimensional model of at least aportion of a heart.
 24. The system according to claim 21, wherein theconduction velocity processor is configured to compute the conductionvelocity for the selected EP data point using the position data of theneighborhood of EP data points and the LAT data of the neighborhood ofEP data points by: defining a plane of positions for the neighborhood ofEP data points using the position data of the neighborhood of EP datapoints; defining a plane of LATs for the neighborhood of EP data pointsusing the LAT data of the neighborhood of EP data points; and computingthe conduction velocity for the selected EP data point according to anintersection between the plane of positions and the plane of LATs. 25.The system according to claim 21, wherein the LAT data are computedrelative to activation at a reference electrode carried by themulti-electrode catheter.
 26. The system according to claim 21, furthercomprising a consistency index processor configured to compute aconduction velocity consistency index for the selected EP data point,wherein the conduction velocity consistency index indicates a degree ofconsistency in a direction of a plurality of conduction velocityconstituents for the selected EP data point.
 27. The system according toclaim 26, wherein the conduction velocity processor is configured tocompute the plurality of conduction velocity constituents for theselected EP data point by computing a respective conduction velocityconstituent for each of a plurality of activation windows of a timesegment.
 28. The system according to claim 26, wherein the conductionvelocity consistency index comprises a ratio of an absolute magnitude ofthe conduction velocity and an average absolute magnitude of theconduction velocity constituents.
 29. The system according to claim 26,wherein the conduction velocity consistency index comprises a ratio ofan absolute magnitude of the conduction velocity and an absolutemagnitude of an average of the conduction velocity constituents.
 30. Thesystem according to claim 26, wherein the conduction velocityconsistency index comprises an average normalized dot product of theconduction velocity constituents and the conduction velocity.